Folic Acid-Adorned Curcumin-Loaded Iron Oxide Nanoparticles for Cervical Cancer.

Cancer is a deadly disease that has long plagued humans and has become more prevalent in recent years. The common treatment modalities for this disease have always faced many problems and complications, and this has led to the discovery of strategies for cancer diagnosis and treatment. The use of magnetic nanoparticles in the past two decades has had a significant impact on this. One of the objectives of the present study is to introduce the special properties of these nanoparticles and how they are structured to load and transport drugs to tumors. In this study, iron oxide (Fe3O4) nanoparticles with 6 nm sizes were coated with hyperbranched polyglycerol (HPG) and folic acid (FA). The functionalized nanoparticles (10-20 nm) were less likely to aggregate compared to non-functionalized nanoparticles. HPG@Fe3O4 and FA@HPG@Fe3O4 nanoparticles were compared in drug loading procedures with curcumin. HPG@Fe3O4 and FA@HPG@Fe3O4 nanoparticles' maximal drug-loading capacities were determined to be 82 and 88%, respectively. HeLa cells and mouse L929 fibroblasts treated with nanoparticles took up more FA@HPG@Fe3O4 nanoparticles than HPG@Fe3O4 nanoparticles. The FA@HPG@Fe3O4 nanoparticles produced in the current investigation have potential as anticancer drug delivery systems. For the purpose of diagnosis, incubation of HeLa cells with nanoparticles decreased MRI signal enhancement's percentage and the largest alteration was observed after incubation with FA@HPG@Fe3O4 nanoparticles.

Highlights

Development of HPG@Fe3O4 nanoparticles for cervical cancer diagnosis and therapy

Increasing the cell selectivity by functionalization of nanoparticles with folic acid (FA)

High loading efficiency and effective delivery of curcumin

Reducing viability of HeLa cells and contribution to diagnosis via MRI contrast

Introduction

The fourth most common malignant gynecological tumor in women is cervical cancer. In 2018, cervical cancer caused 311,000 deaths from 570,000 diagnosed cases.[1] One-half of the number of women that died from cervical cancer were aged ≤58 years, and with the women with ages of 20–39 years, cervical cancer is shown to be the second leading cause of death. Overall, the incidence rate of cervical cancer has demonstrated a decrease in recent years, but distant-stage disease and cervical adenocarcinoma are a threat to the life of many young women around the world, and these cannot often be diagnosed by cytology.[2] Cervical cancer is more common in developing countries compared to developed countries.[3] In addition to cytology for detection of cervical cancer, there have been preventative measures in which vaccination against human papillomavirus is the most important.[4] However, cervical cancer is still a leading cause of death among women and new therapeutic strategies should be designed for its treatment.[5] Nanotechnological approaches including the use of microfluidic devices, high-gravity techniques, microporous smart nanostructures, green methodologies, and combinations would be a great help in order to improve the efficiency, reduce the cost of methods, increase the greenness factors, and also reduce the time of drug/method discovery.[6−9]

Curcumin is a naturally occurring compound derived from rhizome of Curcuma longa.[10] As a bioactive compound, curcumin has been utilized in treatment of various diseases due to its pharmacological and biological activities including anti-oxidant, anti-inflammatory, anti-diabetic, neuroprotective, and more importantly, anti-cancer.[11,12] Curcumin has been administered for treatment of cervical cancer. Curcumin administration (13 μM) stimulates DNA damage in HeLa cells and promotes translocation of p53 and H2A.Xser140 with a route from the cytoplasm to nucleus.[13] Curcumin induces cell cycle arrest at G2/M phases and enhances reactive oxygen species (ROS) generation to stimulate apoptosis and autophagy in reducing the viability of cervical cancer cells.[14] For potentiating the anti-tumor activity of curcumin, its combination with emodin has been administered to inhibit Wnt/β-catenin signaling via TGF-β down-regulation, resulting in reduction in cervical cancer progression.[15] However, owing to poor bioavailability and rapid metabolism of curcumin, this phytochemical is not capable of completely eradicating tumor cells. Therefore, nanoformulations have been developed for its delivery and boosting cancer suppression.[16]

The nanoparticle-based precision medicine leads to formulation of new types of early diagnosis/detection and treatment methods.[17−20] In this regard, the size,[21,22] electronic properties,[23,24] zeta potential,[25] surface functional groups,[26−29] porosity,[30−32] and also the potential interactions[33] affect the possible biomedical applications. In addition, all of these physicochemical parameters should be optimized before addressing the critical issues in the nanomedicine field, in which these optimizations showed critical feedbacks in the diagnosis and treatment perspectives of SARS-CoV-2 as well.[34−36] Iron oxide nanoparticles (IONPs) are extensively utilized for diagnostic aims and MRI contrast due to their superparamagnetic tools, and they show various beneficial characteristics including high solubility and biocompatibility. The IONPs demonstrate biodegradability, they are distributed in different organs of the body, and no long-term toxicity has been reported.[37] A recent experiment revealed the role of folic acid (FA)-modified IONPs in diagnosis of breast cancer.[38] Notably, IONPs can be used for curcumin delivery in cancer treatment. The curcumin-loaded IONPs can suppress SHH signaling and reduce stemness of pancreatic cancer cells to mediate their sensitivity to gemcitabine chemotherapy.[39] Different studies have evaluated the biocompatibility of curcumin-loaded IONPs, and it was found that these nanostructures are distributed in various organs such as the liver, spleen, and brain.[40] They do not induce a significant increase in enzyme levels the in kidney and liver; therefore, they can be utilized as promising therapeutic and diagnostic agents.[41]

Different nanosystems of iron oxide have been developed in order to optimize the drug delivery process, one of which is the polymer nanosystem.[42] Applying biocompatible polymers, including hyperbranched polyglycerol (HPG), in the coating procedure improves the hydrophilicity and facile attachment of targeting agents on the polymer’s surface. HPG is recognized as a favorable new type of polymer, associated with a biocompatible polyether scaffold, well-defined dendrimer-like architecture, and abundant functional end groups.[43] HPG is utilized in the current research in order to coat IONPs prior to incubation with or without FA; FA is under consideration as a targeting agent in view of the known overexpression of FA receptors on some cancerous cells.[44,45] Folate binding protein is known as a glycosylphosphatidylinositol (GPI)-anchored cell surface receptor of folate. FA receptors are observed in small amounts on normal epithelial cell surfaces in various organs, including the kidney, thyroid, lungs, and brain. Of note, they are observed with a high expression ratio in several human tumors. This overabundance of FA receptors on tumor cells might be associated with FA’s vital role in cancer cell proliferation.[46] Recent studies showed that the presence of specific biomarkers on the surface of the nanocarriers would lead to increasing the efficient targeting; however, (over) expression of different types of genes should be investigated before any attempts on this context.[47−49] Also, the iron-based nanoparticles/nanomaterials could be able to mimic the electron transfer between the cellular membranes; therefore, they are completely favorable to make strong interactions with the cells.[50−52]

It is proposed that anticancer drugs bound to HPG-coated magnetic IONPs that have FA attached might achieve increased bioavailability in tumor tissues as a result of targeting via FA receptors.[53,54] A number of studies have applied natural and synthetic polymers to coat IONPs. Huang et al. utilized polyethylene glycol-coated nanoparticles in the doxorubicin transfer process.[55] Akbarzadeh et al. evaluated nanoparticles that were encapsulated into poly(d,l-lactic-co-glycolic acid), poly (ethylene glycol), and (PLGA-PEG) nanoparticles.[56]

Appropriate polymer selection directly depends on the biocompatibility, hydrophilicity, and non-adsorption properties of the given protein. HPG is defined as a type of hydrophilic polyether having unique characteristics including high biocompatibility, minimal toxic effects, and easy synthesis. HPG also contains several terminal hydroxyl groups that are available for the binding of targeted ligands.[57] The synthesis of Fe3O4 nanoparticles using the polyol method was carried out in the current study, and then HPG was added by the anionic ring-opening polymerization method. HPG coating’s impact on Fe3O4 nanoparticles’ biocompatibility enhancement was measured. A covalent bond between FA and polyglycerol’s terminal hydroxyl groups was then generated. The procedure of loading curcumin onto the resultant FA-coupled nanoparticles and consequent evaluation of related loading and releasing efficiencies were then carried out using FT-IR, TEM, DLS, CHNS, and TGA analyses. The cytotoxicity of nanoparticles on HeLa cell lines was evaluated, and mouse L929 fibroblasts as normal cells were used. Finally, the potential of nanoparticles in diagnosis was evaluated by MRI contrast.

Materials and Methods

Synthesis and Surface Functionalization of Fe3O4

IONPs were synthesized by a polyol method and coated with polyglycerol-branched polymers using the looping mechanism. A magnetic stirrer was used to combine 0.53 g of iron(III) acetylacetonate (Fe(acac)3) and 30 mL of triethylene glycol) TREG) components. This mixture was gradually heated until the boiling point was reached (285 °C). It was kept in an atmosphere of N2 for about 30 min under reflux conditions since the heating process was completed within a 3 h period. A black homogeneous solution was obtained. After reaching room temperature, 20 mL of ethyl acetate was added. A neodymium magnet was applied in order to collect the black precipitate. The black precipitate containing uncoated IONPs was washed with ethyl acetate three times in order to remove the additional TREG and was dried under vacuum to a powder form. HPG coating of the nanoparticles was initiated by the addition of 4 mL of glycidol to 30 mg of Fe3O4 nanoparticles and a 1 h sonication process. The black compound was mixed using a magnetic stirring process for 20 h at 140 °C in an atmosphere of N2. Then, the black gel was combined with 15 mL of deionized (DI) water in an ultrasonic bath after reaching room temperature. After exposing this solution to a neodymium magnet, the HPG-coated IONPs (HPG@Fe3O4) were collected and washed with DI water three times and then dried in a vacuum to obtain a black solid. FA was attached to the HPG-coated nanoparticles at concentrations of either 5, 25, or 50% FA. A combination of 5 mg of FA and 100 mg of HPG@Fe3O4 was dissolved in 5 mL of dimethyl sulfoxide (DMSO) to form 5% FA-HPG@Fe3O4 (FA-targeted nanoparticles). A total of 1.53 mg of 4-dimethylaminopyridine (DMAP) and 2.955 mg of ethyl acetate and N,N′-dicyclohexylcarbodiimide (DCC) were added to HPG@Fe3O4 solution as a catalyst and binder, respectively. The heating process took place over 36 h to reach the temperature of 50 °C. The solution was then dialyzed in a 12 kDa molecular weight cutoff dialysis bag to remove the remaining portion of DCC, DMAP, and FA. The retained FA@HPG@Fe3O4 was dried in a freeze dryer.[58,59] FA@HPG@Fe3O4 nanoparticles prepared with 25 and 50% FA were generated using the same procedure (Figure ).

Figure 1

(A) Synthesis of HPG@Fe3O4 and FA@ HPG@Fe3O4 nanoparticles. (B) Schematic illustration of potential applications of folate-targeted for cervical cancer treatment.

Curcumin Loading onto HPG@Fe3O4 and FA@HPG@Fe3O4

Nanoparticles and curcumin were incubated for 24 h at 4 °C and then placed in a shaker at three ratios (1:1, 2:1, and 1:2) with the purpose of loading the curcumin on the nanoparticles. The samples were centrifuged at 4000 rpm for 5 min after 12 h to precipitate the curcumin associated with the nanoparticles.[60,61] The loading efficiency of drug can be calculated using the following equation:

Curcumin Release from HPG@Fe3O4 and FA@HPG@Fe3O4

Curcumin release from HPG@Fe3O4 and FA@HPG@Fe3O4 nanoparticles in phosphate-buffered saline (PBS) at 37 °C was measured during an 8 day period. The nanoparticles with bound curcumin were kept in a dialysis bag (MWCO: 12 kDa) containing a PBS solution for various lengths of time and then centrifuged to determine curcumin release.[62,63] The concentration of released curcumin was measured by absorbance at 450 nm using UV–Vis. The following equation is used in order to calculate the drug release ratio at the initial curcumin level:

In Vitro Cytotoxicity Assay

HeLa cells and mouse L929 fibroblasts were incubated with curcumin (free drug) and nanoparticle-loaded curcumin for 24, 48, and 72 h time intervals. Cytotoxicity was measured in curcumin-treated cells using the 3-(4,5-dimethyl-2-thiazolyl)-2,5-diphenyl-2H-tetrazolium bromide (MTT) assay. Control experiments were carried out using nanoparticle-free medium. Six replications were considered for each experiment. An ELISA reader was utilized in order to read the wells’ optical absorption at 492 nm wavelength.

Cell Uptake of Nanoparticles

HeLa cells were used to determine HPG@Fe3O4 or FA@HPG@Fe3O4 nanoparticle uptake in three 24-well plates at a density of 2000 cells each well. When the cells’ growing phase was achieved after 48 h of incubation at 37 °C, each plate’s medium was replaced with 0.2 mg/mL HPG@Fe3O4 or FA@HPG@Fe3O4 for 1, 3, and 7 μL of 5 M HCl applied for 1 h; an MS2000-Skyray inductively coupled plasma-mass spectrometer (ICP-MS) was used to measure the iron concentration released from the cells.[64]

In Vitro Magnetic Resonance Imaging (MRI) Experiment

T2-weighted signal intensity measurements using a clinical MR scanner (Siemens Magnetom Avanto, 1.5 T) were used to image cells following exposure to nanoparticles. After 24 h of seeding HeLa cells (5 × 105 cells per well) in a 6-well culture plate, various nanocarriers (Fe3O4, HPG@Fe3O4, and FA@HPG@Fe3O4 nanoparticles prepared with 25 wt % FA) were added to cells at a concentration of 0.20 mg/mL. The evaluation of dual targeting impacts on T2-weighted signals was carried out in another experiment through the addition of both HPG@Fe3O4 and FA@HPG@Fe3O4 nanoparticles at a concentration of 0.20 mg/mL to cells. After 24 h, the medium was removed, and consequently, cells were washed three times to eliminate free nanoparticles. Afterward, 3 mL of PBS was added to each well and cells were scanned using a 1.5 T MR scanner (TR1000-4000 ms, TE: 15–480 ms).[65,66]

Characterizations

The characterizations were conducted based on our previous publications.[20,26] A UV–vis spectrometer (Perkin Elmer Lambda 25) was used to record absorbance in the range of 200–800 nm. Fourier transformed infrared spectroscopy (FT-IR) spectrum was obtained using a JASCO FT-IR-460 spectrometer in the range of 400–4000 cm–1. The morphology of synthesized nanoparticles/nanomaterials was observed by a field emission scanning electron microscope (FESEM, TESCAN MIRA-3) under an acceleration voltage of 30–250 kV. Transmission electron microscopy (TEM) analysis was done using a TEM JEOL at 300 kV.

Statistical Analysis

MTT data were obtained from a variance analysis of two constant effects followed by Tukey’s test. The level of significance was considered to be 0.05.

Results and Discussion

Characterization of Nanoparticles

SEM and TEM images were obtained for IONPs (Figure A–D). IONPs prepared without HPG coating showed a uniform size of 5–6 nm (Figure E). HPG-coated nanoparticles were somewhat larger, with a size in the range of 10 nm (Figure F). HPG-coated nanoparticles displayed improved water dispersibility and limited agglomeration that are of important for the purpose of drug delivery (Figure C,D).

Figure 2

SEM and TEM images of (A and C) Fe3O4 and (B and D) HPG@Fe3O4 nanoparticles. Size distribution analysis of (E) Fe3O4 and (F) HPG@Fe3O4 nanoparticles.

FT-IR analyses were used to characterize HPG-coated nanoparticles treated with 5, 25, and 50% FA. FA-adorned nanoparticles demonstrated a significant increase in the vibrational peak rate of 1100, 2900, and 3300 cm–1 for O–H, C–H, and C-O-C bonds, respectively (Figure A). An increase in the peak rate of O–H demonstrates the increased hydrophilicity of HPG-coated nanoparticles treated with FA.[67] The addition of FA to HPG-coated nanoparticles reduced the peak rate of 1100 cm–1. Since the overlap between the primary amines of FA and hydroxyl group makes them invisible,[68] differences are observed in the 3400–3500 and 1560–1640 bands. The peak rate at 1650 cm–1 represents the C=O amide group, while the peak rate at 1700 cm–1 represents the ester. FA-targeted samples with the peak rates of 1400 and 1620 cm–1 belong to pethidine ring and amino-benzoic acid motif, respectively. The peak rate of the C=C bond in six-carbon rings treated with FA was observed in the 1640 band. They could be regarded as the increased peak rates of cover samples.[69]

Figure 3

(A) FT-IR test results of HPG-coated nanoparticles treated with 5, 25, and 50% (top trace) folic acid. (B) TGA curves for Fe3O4 and HPG@Fe3O4 nanoparticles.

Figure B shows the thermal behavior patterns of Fe3O4 and HPG@Fe3O4 nanoparticles. Fe3O4 nanoparticles show a weight reduction of 12% at elevated temperatures, in accordance with the removal of TREG (i.e., 8%) by the weight ratio of Fe3O4:TREG (11.56:1). Weight reduction was continued until the temperature of 285 °C was reached (the boiling point of TREG) and was not changed until heating to 700 °C. The results of FT-IR (Figure A) and elemental analysis, which confirm the existence of organic molecules of TREG on the Fe3O4 surface, imply that the magnetic core of the Fe3O4 nanoparticles is stable despite reaching high temperatures. TGA of HPG@Fe3O4 nanoparticles showed a larger weight reduction at elevated temperatures (i.e., 86.85%), related to the surface polymer degradation.[70,71]

Table provides a list of results of the elemental analysis of HPG-coated and uncoated Fe3O4 nanoparticles. It can be observed that 5.85 and 1.17% of particles’ weights are, respectively, related to C and H elements. Since Fe3O4 and surface-adsorbed TREGs (C6H14O4) constitute Fe3O4 nanoparticles, it could be concluded that the remaining weight% in the elemental analysis (except C and H), i.e., 92.98%, is attributed to Fe and O (from TREG and Fe3O4). Thus, weights% of Fe and O are, respectively, determined to be 63.75 and 28.35%. The number ratio of compounds is determined to be C (6):Fe (23):O (34) based on considering the mentioned weight% ratio. Therefore, 7.5:1 and 11.56:1 are, respectively, determined for Fe3O4:TREG’s number and weight ratio. However, the existence of such a small amount of TREG, which is obtained from the elemental analysis results, supports the conclusions of FT-IR analysis. It should be noted that weights% of Fe3O4 nanoparticles’ C and H atoms calculated after performing the process of HPG grafting are, respectively, determined to be 31.11 and 10.07 (Table ). The C:(Fe + O) ratio is determined to be 31.11:58.82. In this case, C and H are attributed to PG, while TREG and O are attributed to PG, TREG, and Fe3O4. The core of HPG@Fe3O4 is made from Fe3O4, while its shell consists of both TREG and PG. Therefore, it can be concluded that the Fe3O4:TREG:PG’s weight% ratio is 35.98:4.9:59.12, while HPG@Fe3O4’s weight ratio of the core:shell is 35.98:64.02.

Table 1

Elemental Analysis of Fe3O4 and HPG@Fe3O4a

sample	C (wt %) ± SD	H (wt %) ± SD	N (wt %) ± SD	S (wt %) ± SD
Fe3O4	5.85 ± 0.00	1.17 ± 0.00	0.00 ± 0.00	0.00 ± 0.00
HPG@Fe3O4	32.33 ± 0.12	12.17 ± 0.63	0.00 ± 0.00	0.00 ± 0.00

Data represented as mean ± SD (n = 3).

Curcumin Loading and Release

The profiles of curcumin loading and release from HPG@Fe3O4 or FA@HPG@Fe3O4 nanoparticles are shown in Figure A, respectively. Curcumin loading was greatest in HPG@Fe3O4 nanoparticles lacking any FA (85–90% loading), as shown in Figure A. FA@HPG@Fe3O4 nanoparticles that had been prepared using 5% FA showed more curcumin loading than nanoparticles prepared with 25 or 50% FA. The data are consistent with the hypothesis that FA attachment to the nanoparticles impairs the ability of curcumin to permeate into the nanoparticles.

Figure 4

(A) Diagram of loading efficiency for encapsulation of curcumin on 5, 25, and 50% folic acid-coated nanoparticles. (B) In vitro release curve of curcumin release from polyglycerol-coated nanoparticles and 5, 25, and 50% folic acid-targeted nanoparticles.

The rate of curcumin release from HPG@Fe3O4 or FA@HPG@Fe3O4 nanoparticles is shown in Figure B. HPG@Fe3O4 nanoparticles release a higher percentage of their bound curcumin (75%) than FA@HPG@Fe3O4 nanoparticles (45–60%) in vitro. When increasing the concentrations of FA (5, 25, and 50% FA) used to prepare FA@HPG@Fe3O4 nanoparticles, curcumin was released more completely when 5% FA was used and released least effectively when 50% FA was used.

Cultured Cell Viability Following Exposure to Curcumin

The impact of curcumin (free drug) and curcumin-loaded nanoparticles was evaluated in vitro in HeLa cells and mouse L929 fibroblasts. Figure depicts Hela cells (A and B) and L929 cells (C and D) before and after incubation with MTT reagents. The morphology of cells has not changed after exposure to nanoparticles. However, nanoparticles have negatively affected the cell wall that impairs electrostatic interactions among cells and leads to aggregation of cells that is observed for both normal and cancer cells (Figure B,D).

Figure 5

HeLa cell line’s optical microscopy images related to (A) before and (B) after MTT treatment. L929 cell line’s optical microscopy images related to (C) before and after (D) MTT. The scale bar is 50 μm.

The cell viability data presented in Figure (HeLa cells) and Figure (L929 cells) indicate that curcumin-loaded HPG@Fe3O4 nanoparticles did cause considerable cell toxicity to tumor cells (Figure ), but they showed low and negligible toxicity to normal cells (Figure ). Furthermore, the toxicity toward cancer cells is time-dependent and more toxicity is observed after 72 h compared to 24 h on HeLa cells (Figure ). HeLa cells treated with curcumin-loaded FA@HPG@Fe3O4 nanoparticles showed a higher toxicity than the same cells incubated with curcumin-loaded HPG@Fe3O4 nanoparticles. Therefore, functionalization of nanoparticles with FA can promote their selectivity toward cancer cells that is of interest for reducing cancer cell viability (Figure ). In mouse fibroblast L929 cells, incubation with curcumin-loaded FA@HPG@Fe3O4 nanoparticles had a similar effect, with cell viability decreased most when FA@HPG@Fe3O4 nanoparticles prepared with 5% FA were employed. The data in Figures and 7 provide evidence that curcumin-loaded FA@HPG@Fe3O4 nanoparticles are more cytotoxic than curcumin-loaded HPG@Fe3O4 nanoparticles in both cultured cell lines. In addition, as shown in Figures and 7, the cell viability data were generated when HeLa cells (a) and L929 cells (b) were incubated with free curcumin. It is noteworthy that both cell lines were influenced by free curcumin, but with a distinct time profile from the data generated using curcumin-loaded HPG@Fe3O4 or FA@HPG@Fe3O4 nanoparticles. Free curcumin was cytotoxic to both HeLa cells and L929 cells in a 24 h or 48 h incubation, but both cell lines appeared to recover from the cytotoxic effects of free curcumin after 72 h. In contrast, the cytotoxic action of curcumin-loaded onto either HPG@Fe3O4 nanoparticles or FA@HPG@Fe3O4 nanoparticles was observed most strongly after 72 h incubation.

Figure 6

Viability of HeLa cells after exposure to nanoparticles for (A) 24, (B) 48, and (C) 72 h treatment times. Nanoparticles exert their cytotoxicity in a time- and concentration-dependent manner to reduce viability of cancer cells. The lowest viability is observed after 72 h and exposure to HGP@Fe3O4 nanoparticles.

Figure 7

Toxicity evaluation of nanoparticles on L929 fibroblasts as normal cells after (A) 24, (B) 48, and (C) 72 h treatment times. Based on the results, they demonstrate partial toxicity toward normal cells and their overall biocompatibility is promising.

HeLa Cell Uptake of HPG@Fe3O4 or FA@HPG@Fe3O4 Nanoparticles

One of the challenges in cancer therapy is low internalization of anti-cancer agents in tumor cells. Furthermore, anti-tumor compounds, especially plant derived-natural compounds such as curcumin, suffer from poor bioavailability and use of nanocarriers improves its therapeutic index via elevating tumor cell internalization.[72] The aim of the current work is to enhance cancer cell internalization of curcumin using FA-adorned HPG@Fe3O4 nanoparticles. HeLa cells were incubated with HPG@Fe3O4 or FA@HPG@Fe3O4 nanoparticles for 5, 10, and 15 days, and nanoparticle uptake was measured following acid lysis of the cells (Figure A–C). An MS2000-Skyray inductively coupled plasma-mass spectrometer (ICP-MS) was used to measure the iron concentration release from the cells.[67,73] Cellular uptake ranged from 1.5 to 1.7% for HPG@Fe3O4 nanoparticles. Cellular uptake ranged from 1.8 to 2.2% for FA@HPG@Fe3O4 nanoparticles. Therefore, it appears that surface modification of HPG@Fe3O4 nanoparticles with FA promotes their internalization in cervical cancer cells and this property is of importance for effective cancer therapy. Figure D shows the internalization of FA-adorned HGP@Fe3O4 nanoparticles into cervical cancer cells by binding to the folate receptor.

Figure 8

FA@HPG@Fe3O4 uptake through HeLa cells. (A–C) Cellular uptake of nanoparticles by HeLa cells. (D) Schematic representation of FA-adorned HPG IONPs in internalizing in cells and release of curcumin for cervical cancer therapy.

In Vitro MRI of HeLa Cells Incubated with HPG@Fe3O4, FA@HPG@Fe3O4, and Fe3O4 Nanoparticles

The T2-weighted MRI phantom images of HeLa cells incubated with HPG@Fe3O4, FA@HPG@Fe3O4, and Fe3O4 nanoparticles for 24 h can be observed in (Figure ), and quantitative data are shown in Figure . Applying eq , the post-incubation MRI images of the cells achieved through using IONPs are calculated:

Figure 9

(A) T2-weighted MRI phantom images of HeLa cells after incubation with nanocarriers at a concentration of 0.2 mg/mL (a, left) FA@HPG@Fe3O4 (25% w: w FA:polymer), (b) HPG@Fe3O4, (c) control sample, (d, right) Fe3O4 nanoparticles. (B) Signal intensity and increase in in vitro T2-weighted MRI.

The results obtained from the increase in contrasts between various types of nanoparticles are provided in Figure . A reduction of MRI signal enhancement’s percentage was observed in HeLa cells incubated with each type of nanoparticle, with the largest change observed in cells incubated with FA@HPG@Fe3O4 nanoparticles, with 12% targeting ratio (−30.7%). These data are consistent with HeLa cell uptake and viability findings (Figure ). Based on the literature,[74] this type of hyperbranched polymer-coated Fe3O4 nanoparticle is promising due to the trends in the bio-magnetic properties and the slopes between the signal intensities. Fe3O4 nanoparticles have attracted considerable attention due to their significant bio-magnetic properties, but their interactions to the physiological microenvironments and the possible aggregations/agglomerations inhibit/limit their applications. Therefore, using a hyperbranched bioactive and bioavailable polymers could reduce these limitations and increase the constructive interactions.

Conclusions and Remarks

There are novel targeted nanodrugs and delivery systems associated with the ability of increasing the anticancer drugs’ loading and delivery efficiency that can activate the drug-release mechanism. Several investigations were carried out with the purpose of designing and forming anticancer drug-carrier nanosystems.[75,76] The current study describes the synthesis and characterization of small and stable magnetic IONPs, with narrow size distribution, and complexed with HPG hydroxyl groups using the polyol method. The HPG grafting is performed to produce a physiologically stable nanoscale delivery system with high water solubility. FT-IR, TGA, and CHNS elemental analysis confirmed the Fe3O4, HPG@Fe3O4, and FA@HPG@Fe3O4 syntheses, and the nanoparticles’ small size was verified using size analysis. A considerable enhancement of drug aqueous solubility was achieved as a result of the existence of a weak permeation of hydrophobic–hydrophobic linkage into the polyglycerol’s ether backbone. Curcumin loading experiments with the nanoarchitectures confirmed its consequent in vitro release kinetics. The MTT assay revealed the high cytotoxicity of curcumin-loaded FA-adorned HPG@Fe3O4 nanoparticles on HeLa cells and reduction in viability of cancer cells after 24, 48, and 72 h. FA@HPG@Fe3O4 nanoparticles were able to increase the T2-weighted signal intensity during the MRI process. The addition of FA to the poly-hydroxylated HPG@Fe3O4 nanoparticles did increase nanoparticles’ cellular uptake, which leads to the enhancement of the nanocarrier’s therapeutic potential. The FA@HPG@Fe3O4 nanoparticles can bind and release curcumin, and potentially other candidate drugs, for cancer diagnosis and therapy. The MRI test revealed the role of nanostructures in diagnosis of cervical cancer cells; hence, the nanoparticles developed in the current work are promising candidates for treatment and diagnosis of cervical cancer.